Inspection method and apparatus using nuclear magnetic resonance

ABSTRACT

An inspection method by means of an inspection apparatus using nuclear magnetic resonance and having magnetic field generating apparatus for generating a static magnetic field, gradient magnetic fields and an RF magnetic field; magnetic field generating apparatus by means of additional shim coils, which vary homogeneity of the static magnetic field by varying current flowing therethrough; signal detecting apparatus for detecting nuclear magnetic resonance signals from an object to be inspected; an apparatus for processing signals detected by the signal detecting apparatus; and control apparatus for controlling currents flowing through the shim coils, which method using nuclear magnetic resonance comprises a step of storing shim currents corresponding to each of a plurality of slices, capable of improving homogeneity of the static magnetic field for each of the plurality of slices, and a step of switching over the shim currents to those corresponding to a relevant slice to be measured prior to measurements of nuclear magnetic resonance signals from the slice. This inspection method can be applied also to a case where measurements of other slices are effected in intervals of measurements of the relevant slice.

This application is a Continuation of application Ser. No. 08/422,234,filed Apr. 14, 1995 now U.S. Pat. No. 5,602,480.

BACKGROUND OF THE INVENTION

The present invention relates to a measurement method withthree-dimensional images using nuclear magnetic resonance (hereinbelowabbreviated to NMR), and in particular to an inspection method suitablefor measuring simultaneously three-dimensional images of a plurality ofregions.

A magnetic resonance imaging apparatus is one for obtaining tomographicimages using nuclear magnetic resonance phenomena. Usually measurementis effected with two-dimensional images of a specified slice. However,in case where images of a large area are required, two-dimensionalmulti-slice images or three-dimensional images are used for measurement.In a measurement with two-dimensional multi-slice images magneticresonance (NMR) signals from a plurality of slices are measured during awaiting time for magnetization recovery and a plurality oftwo-dimensional images can be obtained in a measurement time for onetwo-dimensional image. By this method, since a region constituting oneimage is in accordance with a region where spin should be excited, S/Ndecreases which decreases slice thickness. In addition, since it isfeared that substantial excitation regions overlap on each other, nomeasurement can be effected in a gapless manner.

On the contrary, for three-dimensional images, a large region is excitedand a plurality of tomographic images can be obtained by phase encoding.For this reason, signal measurement efficiency is high, S/N doesn'tdecrease remarkably, even if slices are thin, and measurement can beeffected in a gapless manner.

The principle of the magnetic resonance imaging explained above isdescribed in detail in "MRI diagnostic (basis and clinic)", Asakurabookseller's, pp. 69-78 (1988). A drawback of the three-dimensionalmeasurement is that measurement time is long, because the number ofrepetitions increases.

However it is possible to shorten the measurement time by applying anultra fast imaging method such as the echo-planar method, etc.,described in Journal of Magnetic Resonance, 29, pp. 355-373 (1978), tothe three-dimensional image measurement.

FIG. 2 is a pulse sequence diagram in case where the conventionalecho-planar method is applied to the three-dimensional imagemeasurement. In FIG. 2 the abscissa represents the time and the ordinaterepresents the intensity of RF pulses, gradient magnetic fields, etc.Further reference numeral 1 is an excitation RF pulse; 2 is a slicinggradient magnetic field applied in a first direction; 3 is a phaseencoding gradient magnetic field applied in the first direction; 4 is aphase encoding gradient magnetic field applied in a second direction; 5is a readout gradient magnetic field applied in the third direction; and6 is a nuclear magnetic resonance signal.

The excitation RF pulse 1 is applied to an object to be inspected at thesame time as the slicing gradient magnetic field 2 to excite a specifiedregion. Spatial information in the first direction is given to thenuclear magnetic resonance signal 6 by applying subsequently thereto thephase encoding gradient magnetic field 3 in the first direction.

Then the nuclear magnetic resonance signal 6 is read out by applyingthereto the readout gradient magnetic field 5 at the same time as thephase encoding gradient magnetic field 4. The nuclear magnetic resonancesignal 6 consists of a plurality of echo signals, each of which has apeak, when the integral of the readout gradient magnetic field 5 iszero.

At this time, since each of the echos includes spatial information inthe direction, in which the readout gradient magnetic field 5 isapplied, and further applied magnitude of the phase encoding gradientmagnetic field 4 differs for different echos, a plurality of echosincluding different spatial information for the application direction ofthe phase encoding gradient magnetic field 4 are measured.

The above procedure is repeated while varying applied magnitude of thephase encoding gradient magnetic field 3 and a three-dimensional imageis obtained by subjecting the measured nuclear magnetic resonance signalto three-dimensional Fourier transformation.

In the ultra fast imaging method, spectroscopic imaging, etc.,inhomogeneity of a static magnetic field below about several ppm, whichis so small that it gives rise to no problem for usual imaging, lowerssignificantly S/N or spectroscopic resolution. Therefore it is desirableto effect a processing to improve homogeneity of the static magneticfield prior to these imagings. However, since static magnetic fielddistribution is distorted by characteristics of the magnet itself,influences of magnetic substances in the neighborhood, susceptibilitydistribution of an object to be examined itself, etc., the processing isgenerally not easy.

Usually a multi-channel coil system called shim coil is incorporated ina magnet for generating the static magnetic field in order to correctthis inhomogeneity of the static magnetic field. The homogeneity of thestatic magnetic field in a region to be imaged is improved bysuperposing shim magnetic fields having various characteristicsgenerated by this multi-channel coil system on the static magnetic fieldgenerated by the static magnetic field coil.

However, since shim coils can generate at most only magnetic fields ofabout third order, it is not possible to correct completely higher orderdistortion in the magnetic field due to the shape of a living body all,etc. over the whole magnet.

Therefore, heretofore, as described e.g. in Magnetic Resonance inMedicine, 18, pp. 335-347 (1991), regulation of the static magneticfield is effected so that distribution of the static magnetic field isuniform only in a region used for the imaging.

For example, when two slices distant by 8 cm from each other are imagedby multi-slice imaging, as indicated in FIG. 3, a set of shim currentsare determined so that the homogeneity of the static magnetic field allover the region including the two slices is best and shim magneticfields are generated according to these shim currents prior to themulti-slice imaging (Step 100). Thereafter different slices are imagedwithout varying the distribution of the magnetic field (Steps 200 and300).

SUMMARY OF THE INVENTION

By the above prior art techniques it is possible to intend to shortenmeasurement time by applying a fast imaging method such as the echoplanar method, etc. to three-dimensional imaging measurement and in casewhere an location of interest has a large area, the three-dimensionalimaging measurement is suitable. However, in case where there exist aplurality of locations of interest, when the prior art three-dimensionalimaging measurement is effected, it is necessary to measure a regionincluding all the locations of interest or to effect measurement bydividing it into several parts. Therefore there was a problem thatmeasurement time was increased.

A first object of the present invention is to provide an inspectionmethod using nuclear magnetic resonance, which can remove such aproblematical point, capable of obtaining three-dimensional images of aplurality of locations of interest without elongating measurement time.

Further, as described previously, it is easy to correct high orderdistortions of the magnetic field by using low order shim magneticfields, if a region where homogeneity of the static magnetic field is tobe improved is restricted to a narrow region, while it becomes moredifficult to obtain distribution of high homogeneity of the staticmagnetic field with increasing area of the region. Consequently, therewas a problem that, by the multi-slice imaging, as described above,imaging should be effected under a condition of lower homogeneity ofstatic magnetic field as that used by single slice imaging and thatimage quality is naturally worsened. Similarly, in case wherespectroscopic measurements are effected for a plurality of localregions, this gives rise to a problem such as worsening in spectroscopicresolution, etc. with respect to a case where the spectroscopicmeasurement is effected for a single local region.

A second object of the present invention is to provide an inspectionmethod and an apparatus using NMR, which can solve the problems of theprior art techniques and which is suitable for multi-slice imaging orspectroscopic measurements of local regions, capable of improving thehomogeneity of the static magnetic field.

The first object of the present invention is an inspection method for aninspection apparatus using NMR comprising means for generating a staticmagnetic field, gradient magnetic fields and an RF magnetic field;magnetic field generating means by additional shim coils, which varyhomogeneity of the static magnetic field by varying current flowingtherethrough; signal detecting means for detecting NMR signals from anobject to be inspected; means for processing signals detected by thesignal detecting means; and means for controlling currents flowingthrough the shim coils (shim currents), which is a method formulti-slice measurements with the help of three-dimensional images of aplurality of local regions by the echo-planar method, the fast SEmethod, the CPMG (Carr--Parcell--Meiboom--Gill) method, etc., dividingthe whole region to be measured in the three-dimensional images intodifferent locations of interest.

This three-dimensional multi-slice measurement is characterized in thatnuclear magnetic resonance signals from different slices are measuredduring waiting time of magnetization recovery. For example, when appliedto the echo-planar method, it comprises a first step of applying thefirst slicing gradient magnetic field (28 in FIG. 1) in the firstdirection and the first excitation pulse (27 in FIG. 1) simultaneouslyto the object to be inspected; a second step of applying thereto thefirst phase encoding gradient magnetic field A (29 in FIG. 1) in thefirst direction, the first readout gradient magnetic field (a part of 31in FIG. 1) in the third direction and the first phase encoding gradientmagnetic field B (a part of 30 in FIG. 1) in the second direction; and athird step of applying the second readout gradient magnetic field (apart of 31 in FIG. 1) in the third direction while repeating polarityinversion at the same time as the second phase encoding gradientmagnetic field B (a part of 30 in FIG. 1) in the second direction toread out nuclear magnetic resonance signals produced as the result of apolarity inversion of the second readout gradient magnetic field and ischaracterized in that a sequence, by which the first step to the thirdstep are repeated desired times, is repeated while varying the phaseencoding gradient magnetic field applied in the first direction toobtain three-dimensional images of the plurality of slices in the objectto be inspected from the readout nuclear magnetic resonance signals.

Further, in measurement for grasping accurately variations in signalintensities such as brain functional imagings, it is characterized inthat three-dimensional multi-slice measurements are effected afterhaving determined the order of measurements of various slices so as tosatisfy a predetermined condition.

Further, when a part of region of each of the left and right brains ismeasured, it is possible to make imaging (measuring) timingsubstantially equal for all the slices and variations in signalintensities of the brains exactly reflect on imaging of the slices bydetermining the order of measurements of the different slices so as tosatisfy N=(1+ne×ns)×ne/ns (where ne denotes the number of applicationsof the phase encoding gradient magnetic fields A for each of the slices;ns the number of slices; and N the sum of ordinal numbers representingthe order of measurements).

The second object of the present invention can be achieved, in casewhere a plurality of slices are imaged continuously by multi-sliceimaging in an inspection method by means of an inspection apparatususing NMR as explained above, by a method and an apparatus, in which aset of optimum shim currents is stored for every slice to be imaged;shim currents are switched over to optimum values for a specified sliceprior to imaging; and then at imaging another slice shim currents areswitched over to optimum values for that slice during imaging waitingtime; or in case where spectroscopic measurements are effected for aplurality of local regions, by a method and an apparatus, in which a setof optimum shim currents is stored for every local region to bemeasured; shim currents are switched over to optimum values for aspecified local region prior to imaging of that local region; and thenat imaging another local region shim currents are switched over tooptimum values for that local region during imaging waiting time.

In a prior art three-dimensional image measurement indicated in FIG. 2,a period of time from application of the excitation RF pulse 1 to theend of measurement of the nuclear magnetic resonance signal 6 is about100 ms. However, when this operation is repeated while varying appliedmagnitude of the phase encoding gradient magnetic field 3, repetitiontime amounts even to several seconds, because a higher S/N of the imagecan be obtained, if magnetization recovery is waited for.

According to the present invention, nuclear magnetic resonance signalscoming from other slices are measured during vacant time in therepetition time by a measurement method (echo-planar method, fast SEmethod, CPMG method, etc.) by which measurement time of the nuclearmagnetic resonance signals is sufficiently short with respect to waitingtime for magnetization recovery. For this reason it is possible toobtain three-dimensional images of a plurality of locations of interest(e.g. brain and abdomen, etc.) without elongating measurement time.

In the inspection method and the apparatus using NMR according to thepresent invention, in case where a plurality of slices are imagedcontinuously by multi-slice imaging, etc., it is unnecessary to takehomogeneity of the static magnetic field into account for the wholeplurality of slices, but only the homogeneity of the static magneticfield of smaller area may be taken into account for each of the slices.That is, by storing such optimum shim currents that the homogeneity ofthe static magnetic field is best for each of the slices and byswitching over shim currents to the optimum values of the correspondingslice at imaging it, it is possible to effect imaging always under thestatic magnetic field of highest homogeneity.

Furthermore, in case where spectroscopic measurements of a plurality oflocal regions are effected, by storing such optimum shim currents thatthe homogeneity of the static magnetic field is best for each of thelocal regions and by switching over shim currents to the optimum valuesof the corresponding local region at imaging it, it is possible toeffect spectroscopic measurements always under the static magnetic fieldof highest homogeneity.

As explained above, according to the present invention, it is possibleto obtain three-dimensional images of a plurality of locations ofinterest without elongating measurement time, because nuclear magneticresonance signals of other slices are measured during a period of timefor waiting for magnetization recovery.

Still further it is possible to realize an inspection method and anapparatus using NMR suitable to multi-slice imaging or spectroscopicmeasurements of local regions and capable of improving the homogeneityof the static magnetic field. More concretely speaking, it is possibleto achieve effects described below.

(1) In case where a plurality of slices are imaged continuously bymulti-slice imaging, etc., since such optimum shim currents that thebest static magnetic field distribution is obtained for each of theslices are stored and the shim currents are switched over to the optimumvalues directly before imaging each of the slices, it is possible torealize an inspection method and an apparatus using NMR capable ofeffecting imaging always under a static magnetic field of highhomogeneity.

(2) In case where spectroscopic measurements are effected for aplurality of local regions, since such optimum shim currents that thebest static magnetic field distribution is obtained for each of thelocal regions are stored and the shim currents are switched over to theoptimum values directly before a spectroscopic measurement of each ofthe local regions, it is possible to realize an inspection method and anapparatus using NMR capable of effecting spectroscopic measurementsalways under a static magnetic field of high homogeneity.

In brief, according to the present invention, in order to obtainthree-dimensional images of a plurality of locations of interest,measurements of nuclear magnetic resonance signals of the locations ofinterest are repeated while varying applied magnitude of the phaseencoding gradient magnetic fields and the three-dimensional images ofthe plurality of locations of interest can be obtained in a measurementtime for one slice without elongating the total measurement time bymeasuring nuclear magnetic resonance signals of other locations ofinterest in vacant time during the repetition time of these measurementsfor the relevant slice.

At this time, shim currents for improving the homogeneity of the staticmagnetic field are stored for each of the slices and multi-slice imagingis effected while switching over shim currents prior to imaging of eachof the slices, corresponding to the relevant slice. Or shim currents forimproving the homogeneity of the static magnetic field are stored foreach of the local regions and spectroscopic measurements of a pluralityof local regions are effected while switching over shim currents priorto imaging of each of the local regions, corresponding to the relevantlocal region.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the echo-planar method isapplied, which is a first embodiment of the present invention;

FIG. 2 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the prior art echo-planarmethod is applied;

FIG. 3 is a diagram indicating a procedure for improving of thehomogeneity of the static magnetic field and multi-slice imagingaccording to prior art techniques;

FIG. 4 is a block diagram indicating an example of construction of anapparatus, to which an inspection method (three-dimensional imagemeasurement) using nuclear magnetic resonance according to the presentinvention is applied;

FIG. 5 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the echo-planar method isapplied, which is a second embodiment of the present invention;

FIG. 6 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the fast SE method isapplied, which is a third embodiment of the present invention;

FIG. 7 is a diagram representing a pulse sequence for athree-dimensional image measurement, in which the CPMG method is appliedto the third embodiment of the present invention;

FIG. 8 is a diagram showing a region of a three-dimensional imagemeasurement, which is a fourth embodiment of the present invention;

FIG. 9 is a diagram showing a region of a three-dimensional imagemeasurement, which is a fifth embodiment of the present invention;

FIG. 10 is a diagram indicating a procedure for regulation of thehomogeneity of the static magnetic field and multi-slice imagingaccording to a sixth embodiment;

FIG. 11 is a diagram indicating a procedure for switching over shimcurrent according to the sixth embodiment;

FIG. 12 is a diagram for explaining improving of the homogeneity of thestatic magnetic field and spectroscopic measurements according to thesixth embodiment;

FIG. 13 is a diagram indicating a procedure for switching over shimcurrent according to the sixth embodiment;

FIGS. 14 and 15 are diagrams indicating pulse sequences for staticmagnetic field measurements according to the sixth embodiment; and

FIG. 16 is a diagram indicating a procedure for switching over shimcurrent according to the sixth embodiment of the present invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Hereinbelow several preferred embodiments of the present invention willbe explained, referring to the attached drawings.

FIG. 4 is a block diagram indicating an example of construction of anapparatus, to which an inspection method (three-dimensional imagemeasurement) using nuclear magnetic resonance according to the presentinvention is applied.

In FIG. 4, reference numeral 7 is a coil for generating the staticmagnetic field; 8 is coils for generating gradient magnetic fields inthree directions, which are a first, a second and a third direction; 9is shim coils for regulating the homogeneity of the static magneticfield; and 10 is an object to be inspected. This object to be inspectedis surrounded by the coils 7, 8 and 9. A sequencer 11 sends commands toa shim power supply 12 to effect control by generating additionalmagnetic fields for correcting inhomogeneity of the static magneticfield by means of the coils 9. The coil 9 consists of a plurality ofchannels and current flowing through each of the coils is controlled bythe sequencer 11 at regulating the homogeneity of the static magneticfield.

The sequencer 11 sends commands also to a gradient magnetic field powersupply 13 and an RF oscillator 14 to control generation of the gradientmagnetic fields and the RF magnetic field. The gradient magnetic fieldsare generated by the coils 8 for generating the gradient magnetic fieldsto add spatial information to signals generated by the object to beinspected. The RF magnetic field is applied to the object to beinspected 10 by an RF transmitter 17 through an RF modulator 15 and anRF amplifier 16. Nuclear magnetic resonance signals generated by theobject to be inspected are received by a receiver 18 to be sent to a CPU20, where they are subjected to signal processing, through an amplifier19, a phase detector 20 and an AD converter 21. If necessary, it ispossible also to store signals and measurement conditions in a memorymedium 23. The shim power supply 12 includes low pass filters 24 and 25having different time constants and a low pass filter is selected by afilter switching section 26, depending on utilization. A shim coil 9 isa double coil, which is constructed so as to obtain an active shieldeffect.

Now the pulse sequence used in the present embodiment will be described.

Since, according to the present invention, nuclear magnetic resonancesignals from other slices are measured in waiting time for magnetizationrecovery, a greater effect can be obtained by a measurement method withdecreasing measurement time sufficiently short for the nuclear magneticresonance signals with respect to the waiting time. Pulse sequences, incase where the echo-planar method and the fast SE method are used asmeasurement methods having such a short measurement time, will beexplained below.

First Embodiment

FIG. 1 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the echo-planar method isapplied, which is the first embodiment of the present invention.

In FIG. 1, reference numerals 27 and 33 are excitation RF pulses; 28 and34 are slicing gradient magnetic fields applied in the first direction;29 and 35 are phase encoding gradient magnetic fields A applied in thefirst direction; 30 and 36 are phase encoding gradient magnetic fields Bapplied in the second direction; 31 and 37 are readout gradient magneticfields applied in the third direction; and 32 and 38 are nuclearmagnetic resonance signals.

In the present embodiment, the excitation RF pulse 27 is applied to theobject to be inspected at the same time as the slicing gradient magneticfield 28 to excite a specified region Sa. Spatial information in thedirection, in which the slicing gradient magnetic field 28 is applied,is added to the nuclear magnetic resonance signal 32 by applyingsubsequently the phase encoding gradient magnetic field A 29 in the samedirection as that direction. Then the nuclear magnetic resonance signal32 is read out by applying the readout gradient magnetic field 31 at thesame time as the phase encoding gradient magnetic field B 30. Thenuclear magnetic resonance signal 32 consists of a plurality of echosignals and each of the echos has a peak when the integral of thereadout gradient magnetic field 31 is zero.

At this time, since each of the echos contains spatial information ofthe application direction of the readout gradient magnetic field 31 andfurther applied magnitude of the phase encoding gradient magnetic fieldB 30 is different for different echos, a plurality of echos containingdifferent spatial information for application direction of the phaseencoding gradient magnetic field B 30 are measured.

A period of time necessary for this procedure is usually 50 to 100 ms.In order to obtain information necessary for forming a three-dimensionalimage, this procedure is repeated desired times while varying appliedmagnitude of the phase encoding gradient magnetic field A 29. Sincethere is a margin of about 400 ms, supposing that this repetition timeis e.g. 500 ms, similar measurements can be effected also for otherslices in this time.

That is, another specified region Sb different from Sa is excited byapplying the excitation RF pulse 33 to the object to be inspected at thesame time as the slicing gradient magnetic field 34. Spatial informationin the direction, in which the slicing gradient magnetic field 34 isapplied, is added to the nuclear magnetic resonance signal 38 byapplying subsequently the phase encoding gradient magnetic field A 35 inthe same direction. Next the nuclear magnetic resonance signal 38 isread out by applying thereto the readout gradient magnetic field 37 atthe same as the phase encoding gradient magnetic field B 36.

Thereafter it is repeated desired times to measure the nuclear magneticresonance signals from the regions Sa and Sb while varying appliedmagnitude of the phase encoding gradient magnetic fields A 29 and 35 toobtain three-dimensional images of the regions Sa and Sb by subjectingrespective nuclear magnetic resonance signals to three-dimensionalFourier transformation.

In the above procedure, switching over of the excited slice can beeffected easily by varying frequency of the excitation RF pulse orintensity of the slicing gradient magnetic field. In case where theintensity of the slicing gradient magnetic field is constant, theinterval between a slice S1 and another slice S0 passing through theorigin of the gradient magnetic fields, is proportional to a differencebetween frequencies for S1 and S0. Further, since the interval isproportional also to the intensity of the slicing gradient magneticfield, switching over of the excited slice can be effected by varyingthe intensity of the gradient magnetic field, fixing the excitationfrequency.

However, in this case, since the thickness of the slice varies, too, itis necessary to vary the pulse width of the excitation RF pulse. Sincethe thickness of the slice is inversely proportional to the intensity ofthe slicing gradient magnetic field and the pulse width of theexcitation RF pulse, in case where the excited slice is switched overe.g. by decreasing the intensity of the slicing gradient magnetic field,it is sufficient to increase the pulse width of the excitation RF pulse.

Although multi-slice measurements by three-dimensional measurement oftwo slices are described in the present embodiment, if there is a marginin the repetition time, it is possible also to apply it tothree-dimensional measurement for more than two slices.

Second Embodiment

FIG. 5 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the echo-planar method isapplied, which is the second embodiment of the present invention.

In FIG. 5, reference numerals 39 and 47 are excitation RF pulses; 40 and48 are slicing gradient magnetic fields applied in the first direction;41 and 49 are phase encoding gradient magnetic fields A applied in thefirst direction; 42 and 50 are inverting RF pulses; 43 and 51 are phaseencoding gradient magnetic fields applied in the first direction; 44 and52 are phase encoding gradient magnetic fields B applied in the seconddirection; 45 and 53 are readout gradient magnetic fields applied in thethird direction; and 46 and 54 are nuclear magnetic resonance signals.

In the present embodiment, the excitation RF pulse 39 is applied to theobject to be inspected at the same time as the slicing gradient magneticfield 40 to excite a specified region Sa. Spatial information in thedirection, in which the slicing gradient magnetic field 40 is applied,is added to the nuclear magnetic resonance signal 46 by applyingsubsequently the phase encoding gradient magnetic field A 41 in the samedirection.

Then the inverting RF pulse 42 is applied thereto at the same time asthe slicing gradient magnetic field 43. The nuclear magnetic resonancesignal 46 is read out by applying the readout gradient magnetic field 45at the same time as the phase encoding gradient magnetic field B 44. Thenuclear magnetic resonance signal 46 consists of a plurality of echosignals and each of the echos has a peak when the integral of thereadout gradient magnetic field 45 is zero.

At this time, since each of the echos contains spatial information ofthe application direction of the readout gradient magnetic field 45 andfurther applied magnitude of the phase encoding gradient magnetic fieldB 44 is different for different echos, a plurality of echos containingdifferent spatial information for application direction of the phaseencoding gradient magnetic field B 44 are measured.

The phase encoding gradient magnetic field A 41 may be applied afterapplication of the inverting RF pulse 42.

A period of time necessary for this procedure is usually 100 ms. Inorder to obtain information necessary for forming a three-dimensionalimage, this procedure is repeated desired times while varying appliedmagnitude of the phase encoding gradient magnetic fields A 41. Sincethere is a margin of about 400 ms, supposing that this repetition timeis e.g. 500 ms, similar measurements can be effected also for otherslices in this time.

That is, another specified region Sb different from Sa is excited byapplying the excitation RF pulse 47 to the object to be inspected at thesame time as the slicing gradient magnetic field 48. Spatial informationin the direction, in which the slicing gradient magnetic field 48 areapplied, is added to the nuclear magnetic resonance signal 54 byapplying subsequently the phase encoding gradient magnetic field A 49 inthe same direction.

Next the inverting RF pulse 50 is applied at the same time as theslicing gradient magnetic field 51 to invert magnetization of the regionSa. The nuclear magnetic resonance signal 54 is read out by applyingthereto the readout gradient magnetic field 53 at the same as the phaseencoding gradient magnetic field B 52.

Also in this case, the phase encoding gradient magnetic field A 49 maybe applied after application of the inverting RF pulse 50.

Thereafter it is repeated desired times to measure the nuclear magneticresonance signals from the regions Sa and Sb while varying appliedmagnitude of the phase encoding gradient magnetic fields A 41 and 49 toobtain three-dimensional images of the regions Sa and Sb by subjectingrespective nuclear magnetic resonance signals to three-dimensionalFourier transformation.

In the above procedure, switching over of the excited slice can beeffected easily by varying frequency of the excitation RF pulse orintensity of the slicing gradient magnetic fields. Similarly the slice,for which magnetization should be inverted, can be switched over byvarying frequency of the inverting RF pulse or intensity of the slicinggradient magnetic fields.

Although multi-slice measurements by three-dimensional measurement oftwo slices are described in the present embodiment, if there is a marginin the repetition time, it is possible also to apply it tothree-dimensional measurement for more than two slices.

Third Embodiment

FIG. 6 is a diagram representing a pulse sequence for athree-dimensional image measurement, to which the fast SE method isapplied, which is the third embodiment of the present invention.

In FIG. 6, reference numerals 55 and 64 are excitation RF pulses; 56 and65 are slicing gradient magnetic fields applied in the first direction;57 and 66 are phase encoding gradient magnetic fields A applied in thefirst direction; 58 and 67 are readout gradient magnetic fields Aapplied in the third direction; 59 and 68 are phase encoding gradientmagnetic fields B applied in the second direction; 60 and 69 areinverting RF pulses; 61 and 70 are slicing gradient magnetic fieldsapplied in the first direction; 62 and 71 are readout gradient magneticfields B applied in the third direction; and 63 and 72 are nuclearmagnetic resonance signals.

In the present embodiment, the excitation RF pulse 55 is applied to theobject to be inspected at the same time as the slicing gradient magneticfield 56 to excite a specified region Sa. Spatial information in thedirections, in which the slicing gradient magnetic field 56 are applied,is added to the nuclear magnetic resonance signal 63 by applyingsubsequently the phase encoding gradient magnetic field A 57 in the samedirection.

Then a procedure in (1) to (3) described below is repeated desiredtimes.

(1) The phase encoding gradient magnetic field B 59 is applied.

(2) The inverting RF pulse 60 is applied at the same time as the slicinggradient magnetic field 61 to invert magnetization of the region Sa.

(3) The nuclear magnetic resonance signal 63 is read out by applying thereadout gradient magnetic field B 62. The nuclear magnetic resonancesignal 63 has a peak, when the integral of the readout gradient magneticfield is zero, and contains spatial information of the applicationdirection of the gradient magnetic field.

At repeating the procedure described in (1) to (3), since appliedmagnitude of the phase encoding gradient magnetic field B 59 is varied,a plurality of nuclear magnetic resonance signals containing differentspatial information for the application direction of the phase encodinggradient magnetic field B 59 are measured. The phase encoding gradientmagnetic field 59 may be applied after application of the inverting RFpulse 60.

Now FIG. 7 is a diagram representing a pulse sequence, in which the CPGMmethod is applied to the present embodiment. In FIG. 7, referencenumerals 87 and 97 are phase encoding magnetic fields B1 applied in thesecond direction (corresponding to 59 and 68 in FIG. 6); 90 and 100 arephase encoding magnetic fields B2 applied in the second direction; 81and 91 are excitation RF pulses (corresponding to 55 and 64 in FIG. 6);82 and 92 are slicing gradient magnetic fields (corresponding to 56 and65 in FIG. 6); 83 and 93 are phase encoding gradient magnetic fields Aapplied in the first direction (corresponding to 57 and 66 in FIG. 6);84 and 94 are readout gradient magnetic fields A applied in the thirddirection (corresponding to 58 and 67 in FIG. 6); 85 and 95 areinverting RF pulses (corresponding to 60 and 69 in FIG. 6); 86 and 96are slicing gradient magnetic fields B applied in the first direction(corresponding to 61 and 70 in FIG. 6); 88 and 98 are readout gradientmagnetic fields applied in the third direction (corresponding to 62 and71 in FIG. 6); and 89 and 99 are nuclear magnetic resonance signals(corresponding to 63 and 72 in FIG. 6).

In order to achieve CPGM, it is necessary to keep the integral of allthe phase encoding gradient magnetic fields applied in the seconddirection from the center of a certain inverting RF pulse to the centerof the succeeding inverting RF pulse at zero. For this purpose thegradient magnetic field (phase encoding gradient magnetic field B2 90)having an absolute value equal to that of the phase encoding gradientmagnetic field B1 87 (corresponding to 59 in FIG. 6) and an invertedpolarity with respect to the latter may be applied after measurement ofthe nuclear magnetic resonance signal 89 (corresponding to 63 in FIG.6), as indicated in FIG. 7.

A period of time necessary for the above procedure is usually about 50to 200 ms, supposing that the procedure described in (1) to (3) isrepeated e.g. eight times. In order to obtain information necessary forforming a three-dimensional image, this procedure is repeated desiredtimes while varying applied magnitude of the phase encoding gradientmagnetic field A 57 in FIG. 6. Since there is a margin of about 300 ms,supposing that this repetition time is e.g. 500 ms, similar measurementscan be effected also for other slices in this time.

That is, another specified region Sb different from Sa is excited byapplying the excitation RF pulse 64 to the object to be inspected at thesame time as the slicing gradient magnetic field 65. Spatial informationin the direction, in which the slicing gradient magnetic field 65 areapplied, is added to the nuclear magnetic resonance signal 72 byapplying subsequently the phase encoding gradient magnetic field A 66 inthe same directions.

Further phase of magnetization in the region is made at random byapplying thereto the readout gradient magnetic field A 67.

Then a procedure in (4) to (6) described below is repeated desiredtimes.

(4) The phase encoding gradient magnetic field B 68 is applied.

(5) The inverting RF pulse 60 is applied at the same time as the slicinggradient magnetic field 70 to invert magnetization of the region Sa.

(6) The nuclear magnetic resonance signal 72 is read out by applying thereadout gradient magnetic field B 71. The nuclear magnetic resonancesignal 72 has a peak, when the integral of the readout gradient magneticfield is zero, and contains spatial information of the applicationdirection of the gradient magnetic field.

At repeating the procedure described in (4) to (6), since appliedmagnitude of the phase encoding gradient magnetic field B 68 is varied,a plurality of nuclear magnetic resonance signals containing differentspatial information for the application direction of the phase encodinggradient magnetic field B 68 are measured.

Also in this case, the phase encoding gradient magnetic field 68 may beapplied after application of the inverting RF pulse 69.

Thereafter it is repeated desired times to measure nuclear magneticresonance signals from the regions Sa and Sb while varying appliedmagnitude of the phase encoding gradient magnetic fields B 59 and 68 andthree-dimensional images of the regions Sa and Sb can be obtained bysubjecting the respective nuclear magnetic resonance signals tothree-dimensional Fourier transformation.

In case where the CPMG method is applied to the procedure described in(4) to (6), the phase encoding gradient magnetic field B2 100 having anabsolute value equal to that of the phase encoding gradient magneticfield B1 97 (corresponding to 68 in FIG. 6) and an inverted polaritywith respect to the latter may be applied after measurement of thenuclear magnetic resonance signal 99 (corresponding to 72 in FIG. 6)from the region Sa, as indicated in FIG. 7.

In the above procedure, switching over of the excited slice can beeffected easily by varying frequency of the excitation RF pulse orintensity of the slicing gradient magnetic fields similarly to thepreceding embodiment.

Similarly the slice, for which magnetization inversion should beeffected, can be switched over by varying frequency of the invertingexcitation RF pulse or intensity of the slicing gradient magneticfields. Although multi-slice measurements by three-dimensionalmeasurement of two slices are described in the present embodiment, ifthere is a margin in the repetition time, it is possible also to applyit to three-dimensional measurement for more than two slices.

Furthermore, although the inverting RF pulse is accompanied byapplication of the slicing gradient magnetic fields and it is designedso as to act only on a specified region in the pulse sequences indicatedin FIGS. 5 and 6, the slicing gradient magnetic fields may not beapplied, when the excitation RF pulse is applied.

In this case, the inverting RF pulse may be a so-called hard pulse,which acts on a large region.

Fourth Embodiment

Here a case where an inspection of a head and an abdomen, e.g. brain andliver, is effected with the help of three-dimensional images by means ofthe apparatus indicated in FIG. 4 will be explained.

For measuring such portions distant from each other, according to priorart techniques, it is necessary to measure a region of about a half ofthe stature or to effect three-dimensional image measurements two times,dividing it into a region including the brain and another regionincluding the liver. Therefore it is easily presumed that measurementtime is tremendous.

In this case, if images of two measurement regions as indicated in FIG.8, region 73 (brain) and region 74 (liver), are measured simultaneouslywhile effecting measurement of a slice in waiting time for magnetizationrecovery of another one, three dimensional images of a plurality ofdesired regions can be measured in a measurement time approximately aslong as that required for measuring either one of them.

In a simultaneous measurement of the head and the abdomen, etc., therespective portions of interest have not always an approximately samevolume. In such a case, in the pulse sequences indicated in FIGS. 1, 5and 6, it is possible also to vary the magnitude of the measurementregion for every slice by varying applied magnitude of the phaseencoding gradient magnetic fields A (29, 35 in FIG. 1; 41, 49 in FIG. 5;and 57, 66 in FIG. 6) for one step.

The magnitude of the measurement region in a direction, in which a phaseencoding gradient magnetic field is applied, is inversely proportionalto applied magnitude of the phase encoding gradient magnetic field forone step. At this time it is possible also to vary magnitude of theexcitation region or the magnetization inversion region, depending onthe magnitude of the measurement region.

The excitation region becomes larger with decreasing pulse width of theexcitation RF pulse (27, 33 in FIG. 1; 39, 47 in FIG. 5; and 55, 64 inFIG. 6) or decreasing applied magnitude of the slicing gradient magneticfield applied at the same time as the excitation RF pulse, while theexcitation region becomes narrower with increasing pulse width orincreasing applied magnitude.

Similarly the magnetization inversion region becomes larger withdecreasing pulse width of the inverting RF pulse (42, 50 in FIG. 5; and60, 69 in FIG. 6) or decreasing applied magnitude of the slicinggradient magnetic fields applied at the same time as the inverting RFpulse. On the contrary the magnetization inversion region becomesnarrower with increasing pulse width of the inverting RF pulse orincreasing applied magnitude.

Fifth Embodiment

In brain function measurement described e.g. in "Science, 254, pp.716-719 (1991)", there is a case where responses of the right and theleft brain are measured separately for a specified stimulus. In such acase, it is not necessary to measure the whole brain, but it issufficient if images of regions of interest in the right and the leftbrain can be obtained. Three-dimensional images of desired regions canbe obtained in a short time, if measurements of other slices areeffected in a waiting time for magnetization recovery so that images ofthe region 75 (right brain) and the region 76 (left brain) are measuredsimultaneously.

In measurements, in which time variations of signals should be treated,such as.the brain function measurement, it is desired to determine orderof measurements (imagings) of different slices so that timings ofimaging (measurement) are approximately equal to each other for all theslices. In order to realize it, the order of measurements may bedetermined so that the sum (be N) of ordinal numbers (numeralsrepresenting the order such as 1st, 2nd, 3rd, . . . ) representing orderof measurements is equal for all the slices. For this purpose N maysatisfy a condition given by Eq. (1);

    N=(1+ne×ns)×ne/ns                              (1)

where ns represents the number of slices and ne indicates the number ofapplications of the phase encoding gradient magnetic fields for each ofslices.

When two slices A and B, e.g. A, B, B, A, A, B, B, A, A, B, B, A, . . ., etc. can be cited, as an example of the order of measurementssatisfying the condition expressed by Eq.(1).

Sixth Embodiment

In case where ultra fast imaging or spectroscopic imaging is effected,it is desirable to regulate homogeneity of the static magnetic fieldprior thereto. Further, in case where images are measured by means of amagnetic resonance imaging apparatus, it is desirable to effect shimmingfor increasing homogeneity of the static magnetic field in order toimprove image quality. For this reason, a usual magnetic resonanceimaging apparatus includes static magnetic field generating coils forshimming called shim coils. These shim coils constitute a multi-channelcoil system having various characteristics such as x, y, z, x2-y2, xy,z2, z3, . . . , etc. For example, x generates a magnetic field varyinglinearly with respect to x-axis and its rate of variation isapproximately proportional to current intensity flowing through the coil(shim current). More homogeneous static magnetic field distribution canbe obtained by superposing these additional static magnetic fields onthe static magnetic field generated by the main coil. Therefore shimmingmeans to obtain such a set of shim currents that they give the optimumstatic magnetic field distribution.

Now, in case where the object to be inspected has a complicated shapesuch as a human body, the static magnetic field distribution can varyonly by about several ppm for different slices. In such a case, it isdifficult to obtain a set of shim currents giving a good result over thewhole measurement region.

Measurements can be effected always under the best static magnetic fielddistribution, if a set of shim currents is obtained so that thehomogeneity of the static magnetic field is optimum for every slice andshim currents are switched over to such values that they give theoptimum static magnetic field distribution for a specified slice, everytime it is measured.

Hereinbelow explanation will be made, taking a case where multi-sliceultra fast imaging is effected by means of the inspection apparatusindicated in FIG. 4 as an example. For example, it is supposed that fiveslices disposed with an interval of 1 cm are imaged continuously.

Regulation of the homogeneity of the static magnetic field consists ofsteps as indicated below.

Step 1: Current--magnetic field characteristics (shim fieldcharacteristics) in a region to be regulated including an imaging regionare examined for each of the shim coils. These shim fieldcharacteristics may be obtained either by calculation or by inserting awater sample, etc. into a space surrounded by the magnets and measuringvariations in the static magnetic field distribution with respect tovariations in shim currents for each of the channels.

Step 2: The static magnetic field distribution in the imaging region ismeasured. At this time it is desired to use a body to be examined, whichshould be imaged in reality, as an object to be measured.

Step 3: A set of such shim currents that they compensate the staticmagnetic field distribution obtained in Step 2, using the shim fieldcharacteristics for each of the channels obtained in Step 1 is found.

Step 4: Shim currents obtained in Step 3 are made flow through the shimcoils.

Thereafter ultra fast imaging, etc. are effected under the improvedstatic magnetic field distribution.

In case where five slices disposed with an interval of 1 cm are imagedcontinuously by multi-slice imaging, etc., the static magnetic fielddistribution can vary by about several ppm at the two ends of the regionto be imaged.

Particularly, in case where the object to be imaged has a complicatedshape such as a human body, this tendency is stronger. Consequently itis difficult to obtain such a set of shim currents that they realize agood static magnetic field distribution over the whole region to beimaged.

Therefore, here, as indicated in Step 124 in FIG. 10, such a set of shimcurrents that they give the most homogeneous static magnetic fielddistribution is obtained for each of the slices to be imaged. That is,in the Step 1, shim field characteristics of the slices are obtained forthe slices, for which the multi-slice imaging is effected; in the Step2, the static magnetic field distribution is measured for each of theslices; and in the Step 3, such a set of shim currents that they givethe best static magnetic field distribution is obtained for each of theslices.

Then, in Step 125, these shim currents for each of the slices are storedin current memory means and imaging is effected after having read outthe shim currents corresponding to the slice to be imaged directlybefore the imaging to make them flow through the shim coils (Steps 126and 127).

Subsequently, when another slice is imaged, imaging is effected afterhaving switched over the shim currents directly before it (Steps 128 and129).

According to the present embodiment, in case where a plurality of slicesare imaged continuously by multi-slice imaging, etc., since the optimumvalues of shim currents giving the best static magnetic fielddistribution for each of the slices are stored and the shim currents areswitched over to the optimum values directly before imaging of therespective slice, imaging can be effected always under a static magneticfield distribution of high homogeneity.

An example of timing of the multi-slice imaging and the switching overof the shim currents is indicated in FIG. 11. That is, Currents 1corresponding to Slice 1 are made flow through the shim coils as initialvalues of the shim currents and imaging of Slice 1 is effected (Steps130 and 131). Directly after the imaging of Slice 1, the shim currentsare switched over to Currents 2 (Step 132).

Subsequently after a predetermined waiting time, imaging of Slice 2 iseffected (Step 133).

Although an embodiment in case where multi-slice ultra fast imaging iseffected has been described in the above explanation, also in case wherespectroscopic measurements of a local region is effected, etc., thespectroscopic measurements can be effected under the best staticmagnetic field distribution for every region to be measured.

That is, as indicated in Step 135 in FIG. 12, such a set of shimcurrents that they give the most homogeneous static magnetic fielddistribution is obtained for each of the local regions to be imaged. Inthe Step 1, shim field characteristics of the slices are obtained forthe local regions, for which the spectroscopic measurements areeffected; in the Step 2, the static magnetic field distribution ismeasured for each of the local regions; and in the Step 3, such a set ofshim currents that they give the best static magnetic field distributionis obtained for each of the local regions.

These shim currents for each of the local regions are stored in currentmemory means (Step 136) and spectroscopic measurements are effectedafter having read out the shim currents corresponding to the localregion to be imaged directly before the spectroscopic measurement tomake them flow through the shim coils (Steps 137 and 138).

Subsequently, when another local region is imaged, spectroscopicmeasurements are effected after having switched over the shim currentsdirectly before them (Steps 139 and 140).

An example of timing of the spectroscopic measurements of local regionsand the switching over of the shim currents is indicated in FIG. 13.That is, Currents 1 corresponding to Local Region 1 are made flowthrough the shim coils as initial values of the shim currents andspectroscopic measurements of Local Region 1 is effected (Steps 141 and142). Directly after the spectroscopic measurements of Local Region 1,the shim currents are switched over to Currents 2 (Step 143).Subsequently after a predetermined waiting time, spectroscopicmeasurements of Local Region 2 are effected (Step 144).

The switching over of currents should be effected, every time the sliceto be imaged or the region to be spectroscopically measured is changed.However it is inconvenient that the repetition time of imaging orspectroscopic measurements is elongated because of this switching time.In order to avoid such a situation, a plurality of low pass filters aredisposed in the shim power supply 12 as indicated in FIG. 4 and the lowpass filter to be used may be switched over by a filter switching oversection 26, depending on utilization.

That is, at switching over the shim current, it may be switched to a lowpass filter 24 (filter 1) having a time constant shorter than thewaiting time of imaging or spectroscopic measurements, while at imagingor spectroscopic measurements, it may be switched to another low passfilter 25 (filter 2) having a long time constant in order not to worsenS/N.

The static magnetic field distribution in the Steps 1 and 2 is obtained,e.g. starting from phase distribution of nuclear magnetic resonancesignals or resonance frequency distribution, using a water sample or abody to be examined.

In case where the static magnetic field distribution is obtained,starting from phase distribution of nuclear magnetic resonance signals,as described e.g. in J. Phys. E: Sci. Instrum., 18, pp. 224-227 (1985),an image of a water sample is photographed by using the pulse sequenceindicated in FIG. 14.

In the figure, 145 is an excitation RF pulse; 146 is an inverting RFpulse; 147 is an echo signal; 148 and 149 are slicing gradient magneticfields applied in a first direction; 150 is a phase encoding gradientmagnetic field applied in a second direction; and 151 is a readoutgradient magnetic field applied in a third direction.

Phase of nuclear magnetization excited by the excitation RF pulse 145 ismade at random by inhomogeneity of the static magnetic field. However,since the phase is inverted at a moment where the inverting RF pulse 146is applied, in case where the interval between the excitation RF pulse145 and the inverting RF pulse 146 is in accordance with the intervalbetween the inverting RF pulse 146 and the echo signal 147, influencesof the inhomogeneity of the static magnetic field are completelycompensated.

However, in FIG. 14, since echo signals including influences of theinhomogeneity of the static magnetic field are measured, the twointervals are set at τ and τ+Δτ, which are differed intentionally by Δτ.At this time, since magnitude of the phase contained in the echo signalsis proportional to the inhomogeneity of the static magnetic field andthe difference Δτ between the two intervals, the static magnetic fielddistribution can be obtained, as indicated by the following Eq.(2):

    θ(x,y)=γ·ΔE(x,y)·Δτ(2)

where θ represents the phase (rad); Δτ the magnetic rotation ratio(rad/(T·sec)); ΔE the inhomogeneity of the static magnetic field (T(Tesler)) and Δτ the difference between the two intervals.

In case where the static magnetic field distribution is obtained,starting from resonance frequency distribution of nuclear magneticresonance signals, as described e.g. in Journal of Magnetic Resonance,85, pp. 244-254 (1989), an spectroscopic image of a homogeneous watersample, etc. is obtained by using the pulse sequence indicated in FIG.15.

In FIG. 15, 152 is an excitation RF pulse; 153 is an inverting RF pulse;154 is an echo signal; 155 and 156 are slicing gradient magnetic fieldsapplied in a first direction; 157 and 158 are phase encoding gradientmagnetic fields applied in a second and a third direction, respectively.

Resonance frequency of water is obtained for every pixel from thespectroscopic imaging. In case where an object to be measured is ahomogeneous sample, the static magnetic field distribution can beobtained by utilizing the fact that displacement in the resonancefrequency Δf(x,y) is proportional to inhomogeneity of the staticmagnetic field, as indicated by Eq. (3):

    Δf(x,y)∝ΔE(x,y)                         (3)

Regulation of the homogeneity of the static magnetic field can beeffected also without measuring the static magnetic field distribution.For example a water sample, etc. are inserted into a space surrounded bythe magnets and using a spectral peak or length of free induction decay(FID) of a specified slice or local region as an evaluation function, aset of shim currents may be determined so that the evaluation functionis improved while varying the shim currents.

In this case, it is supposed that the static magnetic field distributionis most homogeneous, when the value of spectral peak is highest or theFID is longest.

Also in a case where regulation of the homogeneity of the staticmagnetic field is effected in this manner, imaging or spectroscopicmeasurements can be carried out under the best static magnetic fielddistribution by storing a set of optimum shim currents for everyspecified slice or local regions and by making the shim currents, whichare optimum for the corresponding slice or local region, flow throughthe shim coils prior to imaging or spectroscopic measurements.

Now in the regulation of the homogeneity of the static magnetic field,since shim currents are switched over in the waiting time in imaging ofa specified slice or spectroscopic measurements of a specified localregion, there is a possibility that eddy current produced by variationsin the magnetic fields generated by the shim coils worsens image orspectra.

However, in the inspection apparatus used in the embodiment indicated inFIG. 4, an active shield effect can be obtained, if the shim coils 9 aredouble coils, and in this way it is possible to prevent influences ofsuch eddy current. Here active shield is a method, by which magneticfield generated by one part of an double shim coil in a conductorportion such as a magnet, a frame, etc. is compensated by the other partof the double coil. That is, it has a construction, in which no eddycurrent is produced, because no magnetic field is generated in theconductor portion.

For a prior art shim coil it was not supposed to vary current in thecourse of a sequence and thus no production of eddy current wassupposed. Therefore the construction as described above was unnecessary.

On the contrary, by the inspection method according to the presentinvention, active shield is required, because it is necessary to switchover current, depending on the position of the respective slice.

On the active shield, refer to e.g. J. Phys. E: Sci. Instrum., 19, pp.540-545 (1986), in which it is described in detail.

When measurements are repeated while varying applied magnitude of thephase encoding magnetic fields A, using a pulse sequence indicated inFIGS. 1, 5 or 6, the shim currents are switched over according to aprocedure as indicated in FIG. 16. This procedure will be explainedbelow, taking a case where two slices are measured, as an example.

When the applied magnitude is E1, at first shim currents are switchedover to the optimum values for Slice 1 (Step 177) and then Slice 1 ismeasured (Step 178). Next shim currents are switched over to the optimumvalues for Slice 2 (Step 179) and then Slice 2 is measured (Step 180). Asimilar operation is effected after having changed the applied magnitudeto E2. That is, after having switched over the shim currents to theoptimum values for Slice 1 (Step 177'), a measurement of Slice 1 iseffected (Step 178'). Next after having switched over the shim currentsto the optimum values for Slice 2 (Step 179'), a measurement of Slice 2is effected (Step 180'). This operation is repeated, every timemeasurements of Slice 1 and Slice 2 are effected alternately whilevarying applied magnitude of the phase encoding magnetic fields A.

Since this switch over of the shim currents should be effected, everytime the slice to be measured is changed, the time necessary for thisswitch over should be satisfactorily short. For example, in case wherethe repetition time is 500 ms, the measurement time for every encode is100 ms and two slices are measured, the shim currents should be switchedover two times in a vacant period of time of 300 ms.

Usually low pass filters having long time constants are used in the shimcurrent power supply in order to prevent worsening of S/N and thus it isdifficult to switch over the shim currents in 150 ms. In order to avoidsuch a situation, there are disposed a plurality of low pass filters(Filter 1), which may be switched over by a filter switching section 26,as indicated in FIG. 4, depending on field of use.

That is, they may be switched over to a low pass filter 24 having a timeconstant shorter (Filter 1) than the vacant time at switching over theshim currents, while they may be switched over to another low passfilter 25 having a long time constant (Filter 2) at measurements, inorder not to worsen S/N.

It is a matter of course that these embodiments indicate only severalexamples of the present invention and the present invention is notrestricted thereto.

We claim:
 1. An inspection method for measuring a plurality of localregions, using nuclear magnetic resonance by means of an apparatushaving magnetic field generating means for generating a static magneticfield, gradient magnetic fields and an RF magnetic field, magnetic fieldgenerating means including shim coils, which vary homogeneity of saidstatic magnetic field by varying a shim current flowing therethrough,signal detecting means for detecting nuclear magnetic resonance signalsfrom an object to be inspected, means for processing signals detected bysaid signal detecting means, and control means for controlling shimcurrents flowing through said shim coils, said inspection methodcomprising the steps of:(a) obtaining optimum shim current values forimproving the homogeneity of said static magnetic field for each of saidplurality of local regions to be inspected, based on a measurement of astatic magnetic field distribution within each of said plurality oflocal regions, prior to spectroscopic measurement of each of saidplurality of local regions in said object to be inspected; (b) storingsaid optimum shim current values for each of said plurality of localregions; (c) making said shim current of said optimum shim currentvalues flow through said shim coils for another local region to bemeasured subsequently, which is different from a local region alreadyinspected, in a recovery time for longitudinal magnetization inspectroscopic measurements of said local region already inspected; and(d) effecting spectroscopic measurements of said another local region insaid recovery time.
 2. An inspection method according to claim 1,wherein the step of obtaining said optimum shim current values for eachof a plurality of local regions to be inspected includes determiningshim field characteristics for each of the shim coils and measuring thestatic magnetic field distribution within each of the plurality of localregions for said object to be inspected utilizing the shim fieldcharacteristics prior to spectroscopic measurements of the plurality oflocal regions for said object to be inspected so as to determine saidoptimum shim current values for each of the plurality of local regionsto be inspected.